|Publication number||US7181288 B1|
|Application number||US 10/603,243|
|Publication date||20 Feb 2007|
|Filing date||24 Jun 2003|
|Priority date||24 Jun 2002|
|Also published as||US7769470|
|Publication number||10603243, 603243, US 7181288 B1, US 7181288B1, US-B1-7181288, US7181288 B1, US7181288B1|
|Inventors||Ali R. Rezai, John D. Hall, Barry D. Kuban, Ken Baker|
|Original Assignee||The Cleveland Clinic Foundation|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (11), Referenced by (81), Classifications (8), Legal Events (7)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application claims priority to U.S. Provisional Application Nos. 60/391,260 and 60/391,261 both filed Jun. 24, 2002, which are both incorporated by reference in their entireties.
In the case of deep brain stimulation (DBS), it is particularly critical that the stimulation lead be properly positioned. If the lead is not properly positioned and needs to be moved, it must be removed and re-inserted thereby increasing the risk of bleeding and damage to the neural tissue. It is therefore desirable to place the lead within the brain in one attempt and avoid subsequent movement or repositioning of the lead.
These steering techniques, however, are limited to primarily two-dimensional steering since the electrodes are positioned in a linear or planar configuration. In the case of deep brain stimulation (DBS), the stimulation treatment requires stimulation of a volume of neural tissue. Since the exact location of the desired tissue is unknown, it is desirable to steer the electrical field in more than just two-dimensional space.
It will be appreciated that the illustrated boundaries of elements (e.g., boxes or groups of boxes) in the figures represent one example of the boundaries. One of ordinary skill in the art will appreciate that one element may be designed as multiple elements or that multiple elements may be designed as one element. An element shown as an internal component of another element may be implemented as an external component and vice versa.
Further, in the accompanying drawings and description that follow, like parts are indicated throughout the drawings and description with the same reference numerals, respectively. The figures are not drawn to scale and the proportions of certain parts have been exaggerated for convenience of illustration.
The cannula 15 has a proximal end (not shown) for accepting the plurality of leads 20 and a distal end 25 having an opening 30 configured to permit the leads 20 to be advanced out of the opening 30 in the cannula 15. The cannula 15 may be formed from any metal, plastic, or the like, and may be electrically active or inactive depending on the manner in which electrical energy is to be applied.
In one embodiment, each lead 20 has a “pie shaped” cross-section such that all of the leads 20 can form a circular cross-section when the leads 20 are constrained in the cannula 15. For example, each individual lead can be placed adjacent to the other lead 20 such that the flat side of one given lead is in contact with, or closely positioned adjacent to, the flat side of another adjacent lead. Once positioned in the cannula 15, each lead 20 can be prohibited from rotating by the existence of its adjacent leads. It will be appreciated that any number of “pie” shaped leads can be used in the device 10. Additionally, it will be appreciated that two leads 20 can be used in the device 10 having a semi-circular cross-section.
In one embodiment, the electrode bands do not form a continuous electrode surface, but rather the bands are segmented into a plurality of individual electrodes. For example, as shown in
In other embodiments, a single electrode or multiple electrically connected electrodes can extend completely or partially around the perimeter of the lead 20. As can now be appreciated, individual electrodes forming a band can range in an angular distance around the exterior of the supporting surface 40 by as little as a few degrees to as much completely around the supporting surface.
It can now be appreciated that each individual electrode can be selectively powerable. This control provides a desired, focused (i.e. directed) electrical field around the lead 20. For example, electrodes may be powered to stimulate an area adjacent thereto while substantially minimizing the signal in an area adjacent to electrodes on the other side of the lead. Alternatively, opposing electrodes can be powered to produce a signal that destructively interferes with the desired signal. The shape of the field will vary with the power applied, the number and arrangement of electrodes, and particular shapes and sizes chosen for the electrodes.
In operation, the device 10 will be first introduced into the target site as the leads 20 are in the retracted position. Once the device 10 has been implanted, the leads 20 can be moved to the extended position such that the leads 20 are deployed in the desired three-dimensional array. In one embodiment, the leads 20 can diverge radially outwardly from the cannula 15 (located at the target site) into the target site in a uniform pattern, i.e. with the spacing between adjacent electrodes diverging in a substantially uniform and/or symmetric pattern. In the exemplary embodiments, pairs of adjacent leads will be spaced-apart from each other in similar or identical, repeated patterns and will usually be symmetrically positioned about an axis of the cannula 15. The leads 20 may extend or project along generally straight lines from the target site, but will more usually be shaped to curve radially outwardly and optionally to evert proximally so that they face partially or fully in the proximal direction when fully deployed. It will be appreciated that a wide variety of particular patterns can be provided to uniformly cover the region to be treated. Electrical current can then be applied through the electrodes in either a monopolar or bipolar fashion.
In other cases, the cannula 15 may be introduced using an internal stylet which is subsequently exchanged for the electrode array. In this case, the cannula can be relatively flexible since the initial column strength will be provided by the stylet. The cannula serves to constrain the individual leads in a radially collapsed configuration to facilitate their introduction to the tissue target site. The leads can then be deployed to their desired configuration, usually a three-dimensional configuration, by extending distal ends of the electrode elements from the distal end of the cannula into the tissue. In the preferred case of the tubular cannula, this can be accomplished simply by advancing the distal ends of the leads distally from the cannula so that they emerge and deflect (usually as a result of their own spring or shape memory) in a radially outward pattern.
The cannula 515 has a proximal end (not shown) for accepting the plurality of leads 520 and a distal end 525 having an opening 530 configured to permit the leads 520 to be advanced out of the opening 530 in the cannula 515. In one embodiment, the cannula 515 may include tabs 535 to prevent rotational movement of the leads 520 within the cannula 515. The cannula 515 may be formed from any metal, plastic, or the like, and may be electrically active or inactive depending on the manner in which electrical energy is to be applied.
In one embodiment, the plurality of leads 520 can include four outer leads 520 a–d and a central lead 520 e. The outer leads 520 a–d may have a cross section that takes the shape of a “curved” trapezoid, while the central lead 520 e has a circular cross section. In this embodiment, the ends of leads 520 may be rounded (not shown) at the tip to assist in advancing the cannula 515 to the target site in the tissue. It will be appreciated that any number of outer leads can be positioned within the cannula 515. Additionally, the outer leads can take the form of any shape other than a “curved” trapezoid. Obviously, the central lead 520 e can have a cross section different than circular.
Each lead 520 can include a support form or substrate 540 having a plurality of electrodes 545. It will be appreciated that each individual electrode 545 can be selectively powerable. This control provides a desired, focused (i.e. directed) electrical field around each lead 520. Electrodes 545 may be positioned on the inside surface of the lead 520 towards the longitudinal axis of the device 500, on the outside surface of the lead 520 away from the longitudinal axis of the device 500, or combinations thereof. The shape of the field will vary with the power applied, the number and arrangement of electrodes, and particular shapes and sizes chosen for the electrodes. In another embodiment, the central lead 520 e can include a drug infusion channel to provide medication to the target site.
In one embodiment, the leads 520 can be movable between the retracted and extended positions by an actuation mechanism. Illustrated in
In operation, the device 500 will be first introduced into the target site where the leads 520 are in the retracted position. Once the device has been implanted, the leads 520 can be moved to the extended position by advancing the actuation mechanism 600 in an axial direction away from the distal end of the cannula 515 such that the leads 20 are deployed in the desired three-dimensional array. In one embodiment, the leads 520 can diverge radially outwardly from the cannula 515 (located at the target site) into the target site in a uniform pattern, i.e. with the spacing between adjacent electrodes diverging in a substantially uniform and/or symmetric pattern. In the exemplary embodiments, pairs of adjacent leads will be spaced-apart from each other in similar or identical, repeated patterns and will usually be symmetrically positioned about an axis of the cannula 515. It will be appreciated that a wide variety of particular patterns can be provided to uniformly cover the region to be treated.
As shown in
Each lead 825 can include one or more electrodes 840 provided on its distal end such that each can be selectively powerable as discussed above by individually connecting each electrode 840 to a signal generator (not shown) through cables (not shown). Electrodes 840 may be positioned on the inside surface of the lead 825 towards the longitudinal axis of the device 800, on the outside surface of the lead 825 away from the longitudinal axis of the device 800, or combinations thereof. Optionally, the guide 815 may include an electrode 840 positioned at its tip. Electrodes 840 may be selectively powered as an anode, cathode or neither.
In one embodiment, the leads 825 may be coupled to an actuator mechanism similar to the one described above and illustrated in
In operation, as shown in
The present invention may be used to modulate any number of sites in the brain or to modulate particular neuronal bodies which may include neurons, axons, and other constituents of neuronal tissue as is known in the art. As shown in
The present invention may also be implemented alone or in combination with a drug delivery system to provide chemical modulation utilizing a drug, pharmaceutical, or therapeutic agent. In this embodiment, a pump and catheter is provided either alone or in combination with the signal generator and the electrode. The pump may be implanted below the skin of a patient and has a port into which a hypodermic needle can be inserted through the skin to inject a quantity of a liquid agent, such as a drug, pharmaceutical, or therapeutic agent. The liquid agent is delivered from pump through a catheter port into a catheter. The catheter is positioned to deliver the liquid agent to a predetermined region of the brain.
Optionally, the present invention may incorporate a closed-loop feedback system to provide automatic adjustment of the electrical and/or chemical modulation therapy. The system may incorporate a sensor to provide feedback to provide enhanced results. Sensor can be used with a closed loop feedback system in order to automatically determine the level of electrical and/or chemical stimulation necessary to provide the desired treatment. Sensor may be implanted into a portion of a patient's body suitable for detecting symptoms of the disorder being treated. Sensor is adapted to sense an attribute of the symptom to be controlled or an important related symptom. Sensors suitable for this purpose may include, for example, those disclosed in U.S. Pat. No. 5,711,316, which is incorporated herein by reference in its entirety. In cases where the attribute of the symptom is the electrical activity of the brain, stimulating electrodes may be intermittently used to record electrical activity. Alternatively, one or more electrodes implanted within the brain may serve as a sensor or a recording electrode. When necessary, these sensing or recording electrodes may deliver stimulation therapy to the predetermined region of the brain. The output of an external feedback sensor may communicate with the implanted pulse generator through a telemetry down-link.
Furthermore, although the preferred embodiments described above indicate the use of a cannula to enter the brain of a patient, one skilled in the art would appreciate that the present invention may be practiced without the use of a cannula or with a modified cannula.
Also, although the above described preferred embodiments detail that the lead that is capable of being bent, capable of being pre-bent such that the lead has a memory bend, or capable of being pre-formed into a desired shape that has memory such as a shape memory alloy (SMA), the lead still should be stiff enough to be advanced through the cannula, yet flexible enough to be bent as the lead is being advanced through the cannula. Also, the lead may be advanced with or without a stylet. The stylet may provide certain advantages in guiding the lead in the desired direction to reach the predetermined region of the brain.
The operator or patient preferably may also selectively adjust the energy, amplitude or pulse parameters delivered to each electrode. The selective control over each electrode may be achieved by employing a programmer which is coupled via a conductor to a telemetry antenna. The programmer is capable of sending signals via the telemetry antenna to control the electrical signal delivered to the electrodes and to control the actuator system. The system permits attending medical personnel to select the various pulse output options after implant using telemetry communications. While the preferred system employs fully implanted elements, systems employing partially implanted generators and radio-frequency coupling may also be used in the practice of the present invention. Advantageously, the present invention allows the locus of excitation to be selectively adjusted and/or steered to precisely target portions of the brain to achieve the desired treatment therapy. The steering may be accomplished in the manner described in U.S. Pat. No. 5,713,922 which is incorporated herein by reference in its entirety.
To advance lead through the cannula, an actuator system that creates linear motion may be provided (not shown). Two common actuator systems to create linear motion include a linear motor and a rotary motor that is coupled to a sub-system to convert rotary motion to linear motion. If a linear motor is used, then the linear motor would be coupled to the lead to provide the pushing and pulling effect, i.e., the advancement or retraction of the lead. Since the lead requires linear motion (i.e., to advance/retract), rotary motor should be coupled to sub-system such as a lead screw, rack and pinion, or the like to translate rotational motion to linear motion. Both the rotary motor and linear motor may be positioned at the proximal end of cannula or outside the cannula just below the scalp.
The lead may be provided within the cannula as part of the device) or the lead may be installed during the surgical technique. If the lead is provided within the cannula as part of the device, the actuator system (not shown) should be provided at the proximal end of the cannula to control the advancement and retraction of the lead or the actuator system may be positioned outside the cannula just below the scalp. The lead should be flexible enough to be guided along an angled or bent path, yet rigid enough to be advanced or retracted through the guide. Optionally, the lead may be made of a silicon material or metal having a predetermined bend or memory along its body to ensure the lead projects from the aperture at the desired angle.
A component or element may be provided for introducing the cannula to the target site within the treatment region to be treated. For example, a conventional sheath and sharpened obturator (stylet) assembly can be used to initially access the target site. The assembly can be positioned under ultrasonic or other conventional imaging, with the obturator/stylet then being removed to leave an access lumen through the sheath. The leads can then be introduced through the sheath lumen, typically while constrained in the cannula. In some instances, the cannula may be insulated from the deployed electrodes but have an exterior surface configured to provide a common or ground electrode for bipolar operation.
Furthermore, it is understood that one ordinarily skilled in the art can appreciate the ability to select and power individual electrodes independently from other electrodes in order to stimulate the desired target region and to obtain desired directional properties. Specifically, this ability to control the energizing of electrodes enables a physician to focus (i.e. direct) an electrical field around the chosen powered electrode thus pinpointing the stimulation area. For example, if the lead has a circular cross-section and two half ring electrodes wrap around the lead on the same annular ring portion of the lead, but do not touch each other (i.e., there is a gap between them); the present invention provides means for selectively turning on one of the half ring electrodes while turning off the other half ring electrode and vice versa. Accordingly, the half ring electrode that is turned on stimulates an area adjacent thereto while the other half ring electrode that is turned off does not stimulate the area adjacent thereto. Additionally, the shape of the electric field will vary corresponding to the power applied, the number and arrangement of electrodes, and particular shapes and sizes chosen for the electrodes. Also, each electrode may be selectively powered as an anode, cathode or neither.
The present invention also contemplates a navigation system that provides the surgeon/operator with the exact position/orientation of the cannula within the brain after the cannula and lead is deployed in the brain. For example, if the cannula has a circular cross-section (i.e. 360 degrees), it would be helpful for a surgeon/operator to know at which compass direction (i.e., degree) the cannula is positioned relative to a reference point in the brain. Thus, if the surgeon/operator knew exactly where the cannula was positioned, they could make knowledgeable decisions about which electrodes to deploy or turn on. Preferably, the mechanism would be some type of marker that is integral with the cannula, lead, or burr hole device that would show up under a CT or MRI scan. Accordingly, you could print the scan and feed it into a computer having navigational software and a three-dimensional atlas of the patient's brain to model approximately where all of the electrodes are positioned. The software then may be capable of providing you with instructions on where best to deploy the lead or which exact electrodes to turn off or on.
Additionally, the present invention contemplates that the device described above is not only capable of being adjusted intra-operatively, but also is capable of being adjusted post-operatively. Specifically, the lead positioning may be physically adjusted (advanced, retracted, or moved to a different location) in the brain post-operatively through the use of telemetry, RF signals, or other systems known in the art. The cannula need only be inserted once while the lead may be re-positioned in the brain tissue multiple times to reach the desired area of the brain. Further, the electrodes on the lead may be adjusted post-operatively by turning them on/off, adjusting the voltage, adjusting the frequency, and adjusting other electrical signal parameters through the use of telemetry, RF signals, or other systems known in the art. Also, if chemical stimulation is also provided, the ports may be opened or closed or the amount of drug being delivered may be adjusted post-operatively through the use of telemetry, RF signals, or other systems known in the art.
Those skilled in the art will appreciate that electrical properties of the electrodes and the resulting electrical field may be varied by selectively powering individual or groups of electrodes formed from or controlled by micro-electrical mechanical systems (MEMS). Moreover, MEMS actuators may drive electrodes, drug delivery catheters, sensing probes and the like from the cannula to desired locations in an area of interest.
The present invention contemplates methods and implantable systems that ameliorate, prevent or treat a disease condition in the brain or other neuronal tissue. Specifically, this involves combining a method of supplying a source of a genetic expression vehicle with a stimulation device. More specifically, this involves the repopulation of the diseased site with undifferentiated cells or DNA expression vehicles and augmentation of the repopulated cells or DNA expression vehicle with electrical stimulation to cause the newly formed tissue to express desired neurochemicals or neuronal activity.
The repopulation of the neuronal tissue can be carried out using a cellular or a molecular approach. Cellular approaches involve the injection, either directly or via infusion, for example, of undifferentiated cells, preferably cultured autologous cells, into the desired region of the neuronal tissue. Molecular approaches involve the injection, either directly or via infusion, for example, of nucleic acid, whether in the form of naked, plasmid DNA, optionally incorporated into liposomes or other such delivery vehicle or a genetically engineered vector into the area to be treated or enhanced. The genetically engineered vector can include a viral expression vector such as a retrovirus, adenovirus, or an adeno-associated viral vector, for example.
A desired area of neuronal treatment can be determined by one of skill in the art. Near the area of neuronal treatment means within about 1 centimeter (cm) of the edge of the treatment or electrical stimulation area. These regions are shown for example in
The cells or genetic material can be delivered simultaneously with the electrical stimulation device, or they can be delivered separately. In one embodiment, the electrical stimulation device is the carrier of the cells or genetic material. The electrical stimulation device typically includes an implantable stimulator and electrodes.
The nucleic acid molecules, preferably recombinant nucleic acid molecules, can be prepared synthetically or, preferably, from isolated nucleic acid molecules, as is know in the art. A nucleic acid is “isolated” when purified away from other cellular constituents, such as, for example, other cellular nucleic acids or proteins, by standard technique known to those of ordinary skill in the art. The coding region of the nucleic acid molecule can encode a full length gene product or a fragment thereof, or a novel mutated or fusion sequence. The coding sequence can be a sequence endogenous to the target cell, or exogenous to the target cell. The promoter, with which the coding sequence is operably associated, may or may not be one that normally is associated with the coding sequence. Importantly, the present invention allows for genetic information to be turned on or off based upon electrical stimulation provided by the electrical stimulation device. Accordingly, amplitude, intensity, frequency, duration etc. of the electrical signal may be used to selectively control expression of genetic materials or constructs delivered to the target area. U.S. Pat. No. 6,151,525 which is hereby incorporated by reference thereto to the extent it supports the present application describes the use of electrical current to modify undifferentiated contractile cells to form tissue capable of forming new contractile tissue.
The invention has been described with reference to the preferred embodiments. Modifications and alterations will occur to others upon reading and understanding the preceding Detailed Description. It is intended that the invention be construed as including all such modifications and alterations insofar as they come within the scope of the appended claims or the equivalents thereof.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US5868740||24 Mar 1995||9 Feb 1999||Board Of Regents-Univ Of Nebraska||Method for volumetric tissue ablation|
|US6029091 *||9 Jul 1998||22 Feb 2000||Irvine Biomedical, Inc.||Catheter system having lattice electrodes|
|US6050992||19 May 1997||18 Apr 2000||Radiotherapeutics Corporation||Apparatus and method for treating tissue with multiple electrodes|
|US6129685||27 Jun 1997||10 Oct 2000||The University Of Iowa Research Foundation||Stereotactic hypothalamic obesity probe|
|US6185464||4 Mar 1999||6 Feb 2001||Medtronic, Inc.||Arrangement for planting an endocardial cardiac lead|
|US6319241||30 Apr 1999||20 Nov 2001||Medtronic, Inc.||Techniques for positioning therapy delivery elements within a spinal cord or a brain|
|US6343226||30 Sep 1999||29 Jan 2002||Neurokinetic Aps||Multifunction electrode for neural tissue stimulation|
|US6353762||30 Apr 1999||5 Mar 2002||Medtronic, Inc.||Techniques for selective activation of neurons in the brain, spinal cord parenchyma or peripheral nerve|
|US6969388 *||23 Apr 2001||29 Nov 2005||Vnus Medical Technologies, Inc.||Apparatus for applying energy to biological tissue including the use of tumescent tissue compression|
|US7047084 *||20 Nov 2002||16 May 2006||Advanced Neuromodulation Systems, Inc.||Apparatus for directionally stimulating nerve tissue|
|US20020183740||15 Apr 2002||5 Dec 2002||Vidamed, Inc.||Medical probe device and method relationship to copending application|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7765012||27 Jul 2010||Medtronic, Inc.||Implantable medical device including a conductive fixation element|
|US7769472 *||3 Aug 2010||Medtronic, Inc.||Electrical stimulation lead with conformable array of electrodes|
|US7822482||26 Oct 2010||Medtronic, Inc.||Electrical stimulation lead with rounded array of electrodes|
|US7877152 *||25 Jan 2011||JusJas LLC||Bipolar stimulation/recording device with widely spaced electrodes|
|US7945329||17 May 2011||Cranial Medical Systems, Inc.||Multi-channel connector for brain stimulation system|
|US7974705||13 Nov 2009||5 Jul 2011||Proteus Biomedical, Inc.||Multiplexed multi-electrode neurostimulation devices|
|US8010210 *||2 Oct 2008||30 Aug 2011||Medizinische Hochschule Hannover||Apparatus and system for insertion of an implant|
|US8204607 *||19 Jun 2012||Medtronic, Inc.||Implantable medical lead|
|US8224417||17 Jul 2012||Neuronexus Technologies, Inc.||Guide tube for an implantable device system|
|US8321025 *||27 Nov 2012||Cranial Medical Systems, Inc.||Lead and methods for brain monitoring and modulation|
|US8332046||11 Dec 2012||Neuronexus Technologies, Inc.||Neural interface system|
|US8374703 *||26 Jan 2009||12 Feb 2013||Incube Labs, Llc||Method and apparatus for the detection of aberrant neural-electric activity|
|US8406901||27 Apr 2006||26 Mar 2013||Medtronic, Inc.||Sutureless implantable medical device fixation|
|US8467877||21 Nov 2011||18 Jun 2013||Incube Labs, Llc||Method for the detection and treatment of aberrant neural-electric activity|
|US8498720||2 Mar 2009||30 Jul 2013||Neuronexus Technologies, Inc.||Implantable electrode and method of making the same|
|US8565894 *||17 Oct 2008||22 Oct 2013||Neuronexus Technologies, Inc.||Three-dimensional system of electrode leads|
|US8583237||13 Sep 2010||12 Nov 2013||Cranial Medical Systems, Inc.||Devices and methods for tissue modulation and monitoring|
|US8644919||6 Oct 2009||4 Feb 2014||Proteus Digital Health, Inc.||Shielded stimulation and sensing system and method|
|US8731673||31 Oct 2007||20 May 2014||Sapiens Steering Brain Stimulation B.V.||Neural interface system|
|US8738154||24 May 2011||27 May 2014||Proteus Digital Health, Inc.||Multiplexed multi-electrode neurostimulation devices|
|US8774937||1 Dec 2010||8 Jul 2014||Ecole Polytechnique Federale De Lausanne||Microfabricated surface neurostimulation device and methods of making and using the same|
|US8788042||29 Jul 2009||22 Jul 2014||Ecole Polytechnique Federale De Lausanne (Epfl)||Apparatus and method for optimized stimulation of a neurological target|
|US8788064||12 Nov 2009||22 Jul 2014||Ecole Polytechnique Federale De Lausanne||Microfabricated neurostimulation device|
|US8800140||6 Jan 2011||12 Aug 2014||Neuronexus Technologies, Inc.||Method of making a modular multichannel microelectrode array|
|US8805468||7 Jun 2012||12 Aug 2014||Neuronexus Technologies, Inc.||Guide tube for an implantable device system|
|US8831739 *||2 Jun 2006||9 Sep 2014||Huntington Medical Research Institutes||Microelectrode array for chronic deep-brain microstimulation for recording|
|US8849415||8 Apr 2011||30 Sep 2014||Boston Scientific Neuromodulation Corporation||Multi-channel connector for brain stimulation system|
|US8958862||17 Oct 2008||17 Feb 2015||Neuronexus Technologies, Inc.||Implantable device including a resorbable carrier|
|US9044347||15 Aug 2012||2 Jun 2015||The Regents Of The University Of Michigan||Hybrid bioelectrical interface device|
|US9067071||11 Jul 2012||30 Jun 2015||Interventional Autonomics Corporation||System and method for neuromodulation|
|US9072906||26 Jun 2014||7 Jul 2015||Ecole Polytechnique Federale De Lausanne||Apparatus and method for optimized stimulation of a neurological target|
|US9126048||28 Oct 2013||8 Sep 2015||Interventional Autonomics Corporation||Neuromodulation systems and methods for treating acute heart failure syndromes|
|US9155861||20 Sep 2011||13 Oct 2015||Neuronexus Technologies, Inc.||Neural drug delivery system with fluidic threads|
|US9162049||8 Oct 2013||20 Oct 2015||Boston Scientific Neuromodulation Corporation||Devices and methods for tissue modulation and monitoring|
|US9192767||27 May 2014||24 Nov 2015||Ecole Polytechnique Federale De Lausanne||Microfabricated surface neurostimulation device and methods of making and using the same|
|US9220889||11 Feb 2008||29 Dec 2015||Intelect Medical, Inc.||Directional electrode devices with locating features|
|US9220906||29 May 2012||29 Dec 2015||Medtronic, Inc.||Tethered implantable medical device deployment|
|US9265928||13 Dec 2012||23 Feb 2016||Greatbatch Ltd.||Implantable electrode and method of making the same|
|US9308022||10 Dec 2012||12 Apr 2016||Nevro Corporation||Lead insertion devices and associated systems and methods|
|US9314614||31 Oct 2012||19 Apr 2016||Boston Scientific Neuromodulation Corporation||Lead and methods for brain monitoring and modulation|
|US9339197||29 May 2012||17 May 2016||Medtronic, Inc.||Intravascular implantable medical device introduction|
|US9351648||24 Aug 2012||31 May 2016||Medtronic, Inc.||Implantable medical device electrode assembly|
|US9352146||17 Jul 2013||31 May 2016||The Regents Of The University Of Michigan||Peripheral nerve interface devices for treatment and prevention of neuromas|
|US9393427||5 Aug 2014||19 Jul 2016||Cardiac Pacemakers, Inc.||Leadless cardiac pacemaker with delivery and/or retrieval features|
|US9403011||27 Aug 2014||2 Aug 2016||Aleva Neurotherapeutics||Leadless neurostimulator|
|US9440082||19 Jun 2014||13 Sep 2016||Ecole Polytechnique Federale De Lausanne||Microfabricated neurostimulation device|
|US9446240||17 Oct 2014||20 Sep 2016||Interventional Autonomics Corporation||System and method for neuromodulation|
|US20060276866 *||2 Jun 2006||7 Dec 2006||Mccreery Douglas B||Microelectrode array for chronic deep-brain microstimulation for recording|
|US20070027514 *||29 Jul 2005||1 Feb 2007||Medtronic, Inc.||Electrical stimulation lead with conformable array of electrodes|
|US20070027515 *||29 Jul 2005||1 Feb 2007||Medtronic, Inc.||Electrical stimulation lead with rounded array of electrodes|
|US20070150034 *||9 Jun 2006||28 Jun 2007||Medtronic, Inc.||Implantable medical lead|
|US20070255295 *||27 Apr 2006||1 Nov 2007||Medtronic, Inc.||Sutureless implantable medical device fixation|
|US20080027504 *||26 Jul 2007||31 Jan 2008||Cranial Medical Systems, Inc.||Lead and methods for brain monitoring and modulation|
|US20080027508 *||30 Jul 2007||31 Jan 2008||Jus-Jas Llc||Bipolar Stimulation/Recording Device With Widely Spaced Electrodes|
|US20080132981 *||30 Nov 2006||5 Jun 2008||Medtronic, Inc.||Implantable medical device including a conductive fixation element|
|US20080132982 *||30 Nov 2006||5 Jun 2008||Medtronic, Inc.||Method of implanting a medical device including a fixation element|
|US20080208283 *||31 Oct 2007||28 Aug 2008||Rio Vetter||Neural Interface System|
|US20090118806 *||17 Oct 2008||7 May 2009||Vetter Rio J||Three-dimensional system of electrode leads|
|US20090132042 *||17 Oct 2008||21 May 2009||Hetke Jamille F||Implantable device including a resorbable carrier|
|US20090187196 *||17 Oct 2008||23 Jul 2009||Vetter Rio J||Guide tube for an implantable device system|
|US20090204191 *||22 Apr 2009||13 Aug 2009||Jus-Jas Llc||Bipolar Stimulation/Recording Device With Widely Spaced Electrodes|
|US20090204192 *||11 Feb 2008||13 Aug 2009||Intelect Medical, Inc.||Directional electrode devices with locating features|
|US20090234426 *||2 Mar 2009||17 Sep 2009||Pellinen David S||Implantable electrode and method of making the same|
|US20090275818 *||2 Oct 2008||5 Nov 2009||Medizinische Hochschule Hannover||Apparatus and system for insertion of an implant|
|US20090287287 *||19 Nov 2009||Cranial Medical Systems, Inc.||Multi-channel connector for brain stimulation system|
|US20100114272 *||6 Dec 2007||6 May 2010||Sebastian Haidarliu||Multiple micro-wire electrode device and methods|
|US20100191305 *||26 Jan 2009||29 Jul 2010||Mir Imran||Method and apparatus for the detection of aberrant neural-electric activity|
|US20100268055 *||21 Jul 2008||21 Oct 2010||Arizona Board of Regents, a body corporate acting for and on behalf of Arizona State University||Self-Anchoring MEMS Intrafascicular Neural Electrode|
|US20110022124 *||13 Nov 2009||27 Jan 2011||Mark Zdeblick||Multiplexed multi-electrode neurostimulation devices|
|US20110093052 *||2 Aug 2010||21 Apr 2011||Anderson David J||Neural interface system|
|US20110130809 *||13 Nov 2009||2 Jun 2011||Proteus Biomedical, Inc.||Pacing and Stimulation Apparatus and Methods|
|US20110196454 *||13 Nov 2009||11 Aug 2011||Proteus Biomedical, Inc.||Sensing system, device, and method for therapy modulation|
|US20110224757 *||15 Sep 2011||Mark Zdeblick||Multiplexed Multi-Electrode Neurostimulation Devices|
|CN102341036B *||26 Jan 2010||17 Jun 2015||因库博实验室有限责任公司||Method and apparatus for the detection of aberrant neural-electric activity|
|CN103027673A *||1 Nov 2011||10 Apr 2013||财团法人交大思源基金会||Method for identifying stimulation target|
|CN103027673B *||1 Nov 2011||9 Dec 2015||财团法人交大思源基金会||刺激目标范围标定装置|
|EP2783726A1 *||27 Mar 2014||1 Oct 2014||Neurimpulse S.r.l.||Stimulating electrode, particularly for electrical stimulation treatments|
|WO2008068759A2 *||6 Dec 2007||12 Jun 2008||Yeda Research And Development Co.Ltd||Multiple micro-wire electrode device and methods|
|WO2008068759A3 *||6 Dec 2007||22 May 2009||Ehud Ahissar||Multiple micro-wire electrode device and methods|
|WO2009012502A1 *||21 Jul 2008||22 Jan 2009||The Arizona Board Of Regents, A Body Corporate Of The State Of Arizona Acting For And On Behalf Of Arizona State University||Self- anchoring mems intrafascicular neural electrode|
|WO2011121089A1 *||31 Mar 2011||6 Oct 2011||Ecole Polytechnique Federale De Lausanne (Epfl)||Device for interacting with neurological tissue and methods of making and using the same|
|U.S. Classification||607/116, 607/117, 607/118|
|Cooperative Classification||A61N1/0534, A61N1/0529|
|European Classification||A61N1/05K1D, A61N1/05K1|
|21 Nov 2006||AS||Assignment|
Owner name: CLEVELAND CLINIC FOUNDATION, THE, OHIO
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:REZAL, ALI R.;KUBAN, BARRY D.;BAKER, KEN;REEL/FRAME:018620/0412
Effective date: 20061101
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